EP3773281B1 - Gewindeimplantate zur verwendung über knochensegmente hinweg - Google Patents

Gewindeimplantate zur verwendung über knochensegmente hinweg Download PDF

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Publication number
EP3773281B1
EP3773281B1 EP19775637.2A EP19775637A EP3773281B1 EP 3773281 B1 EP3773281 B1 EP 3773281B1 EP 19775637 A EP19775637 A EP 19775637A EP 3773281 B1 EP3773281 B1 EP 3773281B1
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EP
European Patent Office
Prior art keywords
implant
bone
joint
threads
external threads
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
EP19775637.2A
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English (en)
French (fr)
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EP3773281A1 (de
EP3773281A4 (de
Inventor
Derek P. Lindsey
Paul Sand
Bret W. Schneider
Scott A. Yerby
Nikolas F. Kerr
Regina MACBARB
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SI Bone Inc
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SI Bone Inc
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Publication date
Application filed by SI Bone Inc filed Critical SI Bone Inc
Priority to EP24210572.4A priority Critical patent/EP4516267A3/de
Publication of EP3773281A1 publication Critical patent/EP3773281A1/de
Publication of EP3773281A4 publication Critical patent/EP3773281A4/de
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Publication of EP3773281B1 publication Critical patent/EP3773281B1/de
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
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    • A61B17/864—Pins or screws or threaded wires; nuts therefor hollow, e.g. with socket or cannulated
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    • A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/70—Spinal positioners or stabilisers, e.g. stabilisers comprising fluid filler in an implant
    • A61B17/7055—Spinal positioners or stabilisers, e.g. stabilisers comprising fluid filler in an implant connected to sacrum, pelvis or skull
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    • A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
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    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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    • A61F2002/30995—Other joints not covered by any of the groups A61F2/32 - A61F2/4425 for sacro-iliac joints

Definitions

  • Embodiments of the disclosure relate generally to implants for the fixation or fusion of a bone joint or fracture, and more specifically, to threaded implants.
  • Sacroiliac joint (SI-Joint) fusion is a surgical procedure that is performed to alleviate pain coming from the SI-Joint in patients who have failed to receive adequate pain relief with non-surgical treatments of the SI-Joint.
  • SI-Joint fusion arthrodesis
  • degenerative sacroiliitis inflammatory sacroiliitis, iatrogenic instability of the sacroiliac joint, osteitis condensans ilii, or traumatic fracture dislocation of the pelvis.
  • screws and screws with plates were used as the standard instrumentation for sacro-iliac fusion.
  • SI-Joint fusion consisted of an open surgical approach to the SI-Joint from an anterior, a posterior, or a lateral direction. The surgeon would then debride (remove) the cartilage from the articular portion of the j oint and the interosseous ligament from the fibrous portion of the joint. These open approaches require a large incision and deep soft tissue dissection to approach the damaged, subluxed, dislocated, fractured, or degenerative SI-Joint.
  • a typical technique for placing implants involves placement of one or multiple implants from a lateral to medial direction across the SI-Joint. These implants are placed with a starting point on the lateral aspect of the ilium. The implants are then directed across the ilium, across the sacroiliac joint and into the sacrum.
  • US 2015/250513 discloses an intraosseous screw that includes at least one external thread, a receiving element extending into and parallel to the external thread, and connecting members connecting the individual screw threads of the external thread.
  • the or each external thread has capillary through-channels that pass through the screw so as to end in the receiving element.
  • the connecting members define a plurality of through-openings.
  • the receiving element is shaped so as to be able to receive a cylindrical bone portion once the intraosseous screw has been screwed into the bone.
  • WO 2017/147537 discloses compression devices for joining tissue and methods for using and fabricating the same.
  • the present invention provides a threaded implant according to claim 1.
  • Preferred embodiments of the invention are defined in the dependent claims.
  • the threaded implant of the invention comprises an elongated main body having external threads configured to thread into bone, and an internal support structure located within the external threads.
  • the internal support structure has a helical arrangement that extends in an opposite direction to the external threads.
  • the threaded implant may further include a drive socket located on a proximal end of the main body and configured to receive a tip of a drive tool for rotationally driving the implant into bone.
  • a through bore is provided along a central longitudinal axis of the main body from a proximal end to a distal end.
  • the external threads may have a single start and the internal support structure may have four starts.
  • the internal support structure has a pitch that is eight time the pitch of the external threads.
  • the implant may further include fenestrations or interstices between the external threads and the internal support structure.
  • the fenestrations or interstices may be filled with a porous infill which provides scaffolding with increased surface area for new bone growth.
  • the porous infill is at least 20% more porous than the external threads and the internal support structure.
  • the threaded implant can be provided with an elongated main body, a first set of threads, a second set of threads and a sleeve.
  • the main body has a proximal end, a mid-section and a distal end.
  • the first set of threads is provided along the proximal end of the main body and the second set of threads is provided along the distal end.
  • the sleeve is located on the mid-section of the main body such that it may rotate with respect to the main body while being constrained from axial movement.
  • the sleeve has a transverse cross-section that is rectilinear, has at least one apex and/or is triangular in shape.
  • the second set of threads may have a pitch that is greater than a pitch of the first set of threads.
  • the threaded implant can be provided with an elongated main body, a head portion and a threaded portion.
  • the elongated main body has a proximal end, a mid-section and a distal end.
  • the head portion is located on the proximal end of the main body and configured to abut against an outer surface of a bone segment.
  • the threaded portion is located on the distal end of the main body and has a transverse cross-section that is triangular in shape.
  • the implant can be provided with a drive socket located on the proximal end of the main body and configured to receive a tip of a drive tool for rotationally driving the implant into bone.
  • the threaded implant can be provided with an elongated main body, a proximal screw, a proximal screw cap and at least one rotation stop.
  • the elongated main body has a proximal end, a mid-section and a distal end.
  • a joint of a patient can be decorticated or selectively decorticated in order to promote bone regeneration and fusion at the implant site.
  • Many types of hardware are available both for the fixation of bones that are fractured and for the fixation of bones that are to be fused (arthrodesed). While the following examples focus on the SI-Joint, the methods, instrumentation and implants disclosed herein may be used for decortication of other body joints as well.
  • the human hip girdle is made up of three large bones joined by three relatively immobile joints.
  • One of the bones is called the sacrum and it lies at the bottom of the lumbar spine, where it connects with the L5 vertebra.
  • the other two bones are commonly called “hip bones” and are technically referred to as the right ilium and-the left ilium.
  • the sacrum connects with both hip bones at the sacroiliac joint (in shorthand, the SI-Joint).
  • the SI-Joint functions in the transmission of forces from the spine to the lower extremities, and vice-versa.
  • the SI-Joint has been described as a pain generator for up to 22% of lower back pain patients.
  • sacroiliac joint fusion is typically indicated as surgical treatment, e.g., for degenerative sacroiliitis, inflammatory sacroiliitis, iatrogenic instability of the sacroiliac j oint, osteitis condensans ilii, or traumatic fracture dislocation of the pelvis.
  • screws or screws with plates are used for sacro-iliac fusion.
  • articular cartilage may be removed from the "synovial joint" portion of the SI-Joint. This can require a large incision to approach the damaged, subluxed, dislocated, fractured, or degenerated joint. The large incision and removal of tissue can cause significant trauma to the patient, resulting in pain and increasing the time to heal after surgery.
  • screw type implants tend to be susceptible to rotation and loosening, especially in joints that are subjected to torsional forces, such as the SI-Joint. Excessive movement of the implant after implantation may result in the failure of the implant to incorporate and fuse with the bone, which may result in the need to remove and replace the failed implant.
  • FIG. 3 and FIG. 4 illustrate straight implants 10 and 20, respectively, with a solid elongate body 12 or 12' that can be used for the fixation or fusion of two bone segments.
  • the implant 10 shown in FIG. 3 is cylindrical and can optionally have screw threads along the exterior of the implant body. As mentioned above, cylindrical screw type implants can suffer from excessive rotation.
  • the implant 20 in FIG. 4 which has a non-cylindrical cross-sectional area.
  • the implant 20 can have a triangular cross-sectional area, although other rectilinear cross-sectional profiles may be used as well, including rectangular, hexagonal and the like.
  • Non-cylindrical implants need not have a strict rectilinear cross-sectional profile in order to resist rotation.
  • a cross-sectional area that is non-circular will generally suffice.
  • a tear drop shaped cross-sectional area, or a cross-sectional area with at least one apex can resist rotation.
  • Other non-circular cross-sectional geometries that may not have a rectilinear component can also work, such as oval cross-sections.
  • FIG. 5 illustrates insertion of the implant 10 or 20 of FIG. 3 or FIG. 4 across the SI-Joint using a lateral approach that goes laterally through the ilium, across the SI-Joint, and into the sacrum.
  • FIG. 6 illustrates insertion of the same implant across the SI-Joint using a postero-lateral approach entering from the posterior iliac spine of the ilium, angling through the SI-Joint, and terminating in the sacral alae.
  • the implants and instrumentation described herein typically can be inserted across the SI-Joint according to one of these two approaches, or with a similar approach.
  • Elongated, stem-like implant structures 10 or 20 like those shown in FIGS. 3 and 4 make possible the fixation of the SI-Joint in a minimally invasive manner.
  • These implant structures can be effectively implanted through the use a lateral surgical approach (as shown in FIG. 5 ).
  • the procedure may be aided by conventional lateral, inlet, and outlet visualization techniques, e.g., using X-ray image intensifiers such as a C-arms or fluoroscopes to produce a live image feed, which is displayed on a TV screen.
  • one or more implant structures 20 are introduced laterally through the ilium, the SI-Joint, and into the sacrum. This path and resulting placement of the implant structure(s) 20 are best shown in FIGS. 9 and 10 . In the drawing, three implant structures 20 are placed in this manner. Also in the drawing, the implant structures 20 are rectilinear in cross section and triangular in this case, but it should be appreciated that implant structures 20 of other rectilinear cross sections can be used. Additionally, in some procedures (not discussed in further detail herein), implants may be introduced into the SI-Joint from an anterior direction. Further information on anterior techniques may be found in co-pending U.S. patent application Pub. No. 2015/0105828 filed October 15, 2014 and entitled "Implant Placement" . The decortication instruments and methods disclosed herein and variants thereof may also be utilized in these anterior procedures.
  • the physician diagnoses the SI-Joint segments that are to be fixated or fused (arthrodesed) using, e.g., the Fortin finger test, thigh thrust, FABER, Gaenslen's, compression, distraction, and or diagnostic SI-Joint injection.
  • the physician Aided by lateral, inlet, and outlet C-arm views, and with the patient lying in a prone position, the physician aligns the greater sciatic notches and then the alae (using lateral visualization) to provide a true lateral position.
  • a 3 cm incision is made starting aligned with the posterior cortex of the sacral canal, followed by blunt tissue separation to the ilium.
  • the guide pin 38 (with pin sleeve (not shown)) (e.g., a Steinmann Pin) is started resting on the ilium at a position inferior to the sacrum end plate and just anterior to the sacral canal.
  • the guide pin 38 In the outlet view, the guide pin 38 should be parallel to the sacrum end plate at a shallow angle anterior (e.g., 15 degree to 20 degree off the floor, as FIG. 10 shows). In a lateral view, the guide pin 38 should be posterior to the sacrum anterior wall. In the outlet view, the guide pin 38 should be superior to the first sacral foramen and lateral of mid-line. This corresponds generally to the sequence shown diagrammatically in FIGS. 7A and 7B . A soft tissue protector (not shown), and a drill sleeve (not shown) within the soft tissue protector, may be slipped over the guide pin 38 and firmly against the ilium before removing the guide pin sleeve (not shown).
  • a pilot bore 42 may be drilled with cannulated drill bit 40, as is diagrammatically shown in FIG. 7C .
  • the pilot bore 42 may extend through the ilium, through the SI-Joint, and into the sacrum.
  • the drill bit 40 and drill sleeve (not shown) are then removed.
  • a shaped broach 44 may be tapped into the pilot bore 42 over the guide pin 38 (and through the soft tissue protector, not shown) to create a broached bore 48 with the desired profile for the implant structure 20, which in the drawing is triangular. This generally corresponds to the sequence shown diagrammatically in FIG. 7D .
  • the triangular profile of the broached bore 48 is also shown in FIG. 8 .
  • FIGS. 7E and 7F illustrate the assembly of a soft tissue protector or dilator or delivery sleeve 200 with a drill sleeve 202, a guide pin sleeve 204 and a handle 206.
  • the drill sleeve 202 and guide pin sleeve 204 can be inserted within the soft tissue protector 200 to form a soft tissue protector assembly 210 that can slide over the guide pin 208 until bony contact is achieved.
  • the soft tissue protector 200 can be any one of the soft tissue protectors or dilators or delivery sleeves disclosed herein.
  • an expandable dilator or delivery sleeve 200 can be used in place of a conventional soft tissue dilator.
  • the expandable dilator in some procedures, can be slid over the guide pin and then expanded before the drill sleeve 202 and/or guide pin sleeve 204 are inserted within the expandable dilator. In other procedures, insertion of the drill sleeve 202 and/or guide pin sleeve 204 within the expandable dilator can be used to expand the expandable dilator.
  • a dilator can be used to open a channel though the tissue prior to sliding the soft tissue protector assembly 210 over the guide pin.
  • the dilator(s) can be placed over the guide pin, using for example a plurality of sequentially larger dilators or using an expandable dilator.
  • the dilator(s) can be removed and the soft tissue protector assembly can be slid over the guide pin.
  • the expandable dilator can serve as a soft tissue protector after being expanded. For example, after expansion the drill sleeve and guide pin sleeve can be inserted into the expandable dilator.
  • a triangular implant structure 20 can be now tapped through the soft tissue protector over the guide pin 38 through the ilium, across the SI-Joint, and into the sacrum, until the proximal end of the implant structure 20 is flush against the lateral wall of the ilium (see also FIGS. 5 and 10 ).
  • the guide pin 38 and soft tissue protector are withdrawn, leaving the implant structure 20 residing in the broached passageway, flush with the lateral wall of the ilium (see FIGS. 5 and 10 ).
  • two additional implant structures 20 are implanted in this manner, as FIG. 9 best shows.
  • the proximal ends of the implant structures 20 are left proud of the lateral wall of the ilium, such that they extend 1, 2, 3 or 4 mm outside of the ilium. This ensures that the implants 20 engage the hard cortical portion of the ilium rather than just the softer cancellous portion, through which they might migrate if there was no structural support from hard cortical bone.
  • the hard cortical bone can also bear the loads or forces typically exerted on the bone by the implant 20.
  • the implant structures 20 are sized according to the local anatomy.
  • representative implant structures 20 can range in size, depending upon the local anatomy, from about 35 mm to about 60 mm in length, and about a 7 mm inscribed diameter (i.e. a triangle having a height of about 10.5 mm and a base of about 12 mm).
  • the morphology of the local structures can be generally understood by medical professionals using textbooks of human skeletal anatomy along with their knowledge of the site and its disease or injury. The physician is also able to ascertain the dimensions of the implant structure 20 based upon prior analysis of the morphology of the targeted bone using, for example, plain film x-ray, fluoroscopic x-ray, or MRI or CT scanning.
  • one or more implant structures 20 can be individually inserted in a minimally invasive fashion across the SI-Joint, as has been described.
  • Conventional tissue access tools, obturators, cannulas, and/or drills can be used for this purpose.
  • the novel tissue access tools described above and in U.S. Provisional Patent Application No. 61/609,043, titled “TISSUE DILATOR AND PROTECTOR” and filed March 9, 2012 , and in U.S. Published Application No. 2017/0007409, titled “SYSTEMS, DEVICES, AND METHODS FOR JOINT FUSION” and filed July 12, 2016 can also be used.
  • No joint preparation, removal of cartilage, or scraping are required before formation of the insertion path or insertion of the implant structures 20, so a minimally invasive insertion path sized approximately at or about the maximum outer diameter of the implant structures 20 can be formed.
  • the implant structures 20 can obviate the need for autologous bone graft material, additional pedicle screws and/or rods, hollow modular anchorage screws, cannulated compression screws, threaded cages within the joint, or fracture fixation screws. Still, in the physician's discretion, bone graft material and other fixation instrumentation can be used in combination with the implant structures 20.
  • implant structures 20 can be used, depending on the size of the patient and the size of the implant structures 20.
  • the patient After installation, the patient would be advised to prevent or reduce loading of the SI-Joint while fusion occurs. This could be about a six to twelve week period or more, depending on the health of the patient and his or her adherence to post-op protocol.
  • the implant structures 20 make possible surgical techniques that are less invasive than traditional open surgery with no extensive soft tissue stripping.
  • the lateral approach to the SI-Joint provides a straightforward surgical approach that complements the minimally invasive surgical techniques.
  • the profile and design of the implant structures 20 minimize or reduce rotation and micromotion.
  • Rigid implant structures 20 made from titanium provide immediate post-op SI-Joint stability.
  • a bony in-growth region 24 comprising a porous plasma spray coating with irregular surface supports stable bone fixation/fusion.
  • the implant structures 20 and surgical approaches make possible the placement of larger fusion surface areas designed to maximize post-surgical weight bearing capacity and provide a biomechanically rigorous implant designed specifically to stabilize the heavily loaded SI-Joint.
  • a fenestrated matrix implant may be used, providing cavities in which to pack bone growth material, and or providing additional surface area for bone on-growth, in-growth and or through-growth.
  • the implant can be inserted across three or more cortical walls. For example, after insertion the implant can traverse two cortical walls of the ilium and at least one cortical wall of the sacrum.
  • the cortical bone is much denser and stronger than cancellous bone and can better withstand the large stresses found in the SI-Joint.
  • the implant can spread the load across more load bearing structures, thereby reducing the amount of load borne by each structure.
  • movement of the implant within the bone after implantation is reduced by providing structural support in three locations around the implant versus two locations.
  • the implant(s) 10 or 20 may be placed in the implant bore(s) 48 ( FIG. 8 ) using a generally medial or axial, non-rotational force, such as tapping an implant into place using a slide hammer.
  • the external threads of the present implant may be threaded into place by applying a rotational force, as will now be described.
  • Implant 300 is provided with external threads 310 and an internal counter-rotating support structure 312.
  • proximal end 314 may be provided with a hexagonally shaped socket 315 for receiving a drive tool (not shown) when implant 300 is being inserted or removed.
  • a through bore 316 may be provided along the central axis from the proximal end 314 to the distal end 318.
  • External threads 310 are used to engage bone when threading implant 300 across a bone joint.
  • external threads 310 are self-tapping.
  • internal counter-rotating support structure 312 extends helically in an opposite direction from external threads 310 as shown.
  • Support structure 312 provides stiffness and torsional rigidity to implant 300 while permitting fenestrations between external threads 310 for promoting better bony on-growth, ingrowth and/or through-growth.
  • a single external thread 310 helically extends from near the proximal end 314 to the distal end 318 of implant 300. In other embodiments (not shown), multiple starts of external threads 310 may be employed.
  • internal counter-rotating support structure 312 comprises four starts. In other embodiments (not shown), fewer or more starts may be employed. In this embodiment, internal counter-rotating support structure 312 has a pitch that is eight times the pitch of external threads 310. In other embodiments (not shown), the pitch of structure 312 may be less or more than eight times that of threads 310. Support structure 312 may comprise layers. In some embodiments, these layers alternate in direction.
  • the fenestrations or interstices between external threads 310 and internal counter-rotating support structure 312 are filled with porous infill 320.
  • Infill 320 provides scaffolding with a large surface area for new bone growth.
  • Infill 320 can also add additional strength to implant 300 in compression, tension, torsion, bending, shear, etc., but still allow for better bony on-growth, ingrowth and/or through-growth than if the fenestrations or interstices were completely filled with less porous material.
  • the exploded view of FIG. 12 shows main portion 322 of implant 300 separately from the porous infill 320 for clarity, although in this embodiment infill 320 is a collection of many individual segments rather than an interconnected structure.
  • main portion 322 may also be porous, but having a different porosity than infill 320.
  • Infill 320 may be at least 20% more porous than main portion 322. Both may be made together in the same manufacturing process, such as 3D printing or other additive manufacturing process.
  • infill 320 is formed from the same material as main portion 322, while in other embodiments a different material or materials may be used to form infill 320.
  • porous infill 320 has the same inner diameter as that of the main portion 322 of implant 300, forming a continuous surface defining through bore 316, as shown in FIG. 13 .
  • the outer diameter of infill 320 may be the same diameter of the radially inward end of the tapered portions of threads 310, thereby forming the root diameter of threads 310.
  • the inner and outer diameters of counter-rotating support structure 312 may also be the same as those of infill 320, such that breaks 324 are formed in infill 320 (as seen in FIG. 12 ) to accommodate structure 312.
  • An implant bore may be formed across a bone segment before implant 300 is threaded into it.
  • the diameter of the bore is approximately the same as the root diameter of threads 310.
  • a tap may be used to create internal threads inside the bone before implant 300 is inserted.
  • self-boring and/or self-tapping features are provided on implant 300.
  • Implant 300 may be threaded into the bore until just the proximal head portion protrudes from the bone.
  • proximal head portion may be partially or fully recessed into the bone, or flush with the outer surface of the bone.
  • Implant 340 comprises a main body 350 having a proximal end 352, a mid-section 354 and a distal end 356.
  • Proximal end 352 is provided with a first set of threads 358 while distal end 356 is provided with a second set of threads 360.
  • mid-section 354 has a constant diameter configured to receive triangle sleeve 362 (as shown in FIG. 14 ) such that it may rotate with respect to main body 350 while being constrained from axial movement.
  • proximal end 352 of main body 350 may be provided with a hexagonally shaped socket 364 for receiving a drive tool (not shown) when implant 340 is being inserted or removed.
  • a through bore 366 may be provided along the central axis from the proximal end 352 to the distal end 356.
  • main body 350 may be provided with a constant root or minor diameter taper that extends from a smaller diameter 368 at distal end 356 to a larger diameter 370 closer to proximal end 352, except for mid-section 354 which has a smaller diameter than the tapered root or minor diameter sections adjacent to it.
  • the first set of threads 358 may have a constant outer or major diameter 372, such that threads 358 protrude radially less from the root or minor diameter as they extend proximally along main body as shown in FIG. 16 .
  • the second set of threads 360 may have a constant outer or major diameter 374 (larger than the outer or major diameter 372 of the first set of threads 358), such that threads 360 protrude radially less from the root or minor diameter as they extend proximally along main body as shown in FIG. 16 .
  • the pitch of distal threads 360 is greater than the pitch of proximal threads 372.
  • This arrangement causes implant 340 to advance more rapidly in relation to a distal bone segment that it does relative to a more proximal bone segment, thereby drawing the two bone segments closer together (e.g. compressing a joint between the two bone segments) when the implant is tightened into place.
  • one or more fenestrations 376 may be provided in triangle sleeve 362 such that they communicate with a space around mid-section 354. Fenestrations 376 provide additional area for on-growth, ingrowth and through-growth of new bone tissue after implantation of device 340. During implantation, bone chips may be placed inside fenestrations 376 to aid in new bone growth.
  • Chamfers 378 (also shown in FIG. 17 ) may be provided along the apexes of triangle sleeve 362.
  • One advantage to providing chamfers 378 is that stress concentrations are avoided when creating a bore through the bone for implant 340 to reside in.
  • Device 340 may be implanted in bone in a manner similar to previously described devices.
  • Triangle sleeve 362 may be provided with tapered leading edges (as shown in FIG. 14 ), self-broaching features (not shown), and/or a separate broaching instrument (not shown) may be used to create a triangularly shaped bore before device 340 is implanted.
  • triangle sleeve 362 resides across a gap between two bone segments once device 340 is in place.
  • a triangularly shaped bore may be broached just deep enough to accommodate triangle sleeve 362, but not all the way to the distal tip of device 340.
  • the full depth of threads 358 extends beyond the flats of triangle sleeve 362 and into the surrounding bone, as depicted in FIG. 17 .
  • triangle sleeve 362 may freely rotate with respect to main body 350 such that it travels axially into the triangularly shaped bore in the bone without rotating while main body 350 is rotated and advances with threads 360 and 358.
  • bone in-growth and through-growth after implantation causes triangle sleeve 362 to become rigid with main body 350. This mechanism inhibits implant 340 from backing out of the bone or migrating further into it, since triangle sleeve 362 is prevented from rotating by the surrounding triangularly shaped bore in the bone.
  • a mechanism such as a toggle, cam, or other feature can be activated immediately after implantation to lock triangle sleeve 362 to main body 350, thereby providing immediate anti-rotation.
  • Implant 400 comprises a main body 410 having a proximal end 412, a mid-section 414 and a distal end 416.
  • Proximal end 412 is provided with a head portion 418 configured to abut against an outer surface of a bone segment when implant 400 is implanted therein.
  • Distal end 416 is provided with a threaded portion 420 having a triangular cross-section, as best seen in FIGS. 18 and 21 .
  • Mid-section 414 may have a constant diameter that extends radially to the same extent as the flat portions of the triangular cross-section. As shown in FIG.
  • proximal end 412 may be provided with a hexagonally shaped socket 422 for receiving a drive tool (not shown) when implant 400 is being inserted or removed.
  • a through bore 424 may be provided along the central axis from the proximal end 412 to the distal end 416.
  • threaded portion 420 of implant 400 is provided with external threads 426 and an internal counter-rotating support structure 428.
  • External threads 426 are used to engage bone when threading implant 400 across a bone joint.
  • external threads 426 are self-tapping.
  • internal counter-rotating support structure 428 extends helically in an opposite direction from external threads 426 as shown. Support structure 428 provides stiffness and torsional rigidity to implant 400 while permitting fenestrations between external threads 426 for promoting better bony on-growth, ingrowth and/or through-growth.
  • a single external thread 426 helically extends from near the distal end 416 to the mid-section 414 of implant 400, although the thread is interrupted and has portions removed by the flat sides of the triangular cross-section.
  • multiple starts of external threads 426 may be employed.
  • internal counter-rotating support structure 428 comprises four starts. In other embodiments (not shown), fewer or more starts may be employed.
  • internal counter-rotating support structure 428 has a pitch that is eight times the pitch of external threads 426. In other embodiments (not shown), the pitch of structure 428 may be less or more than eight times that of threads 426, and or may form a shape other than helical.
  • the fenestrations or interstices of implant 400 between external threads 426 and internal counter-rotating support structure 428 are filled with porous infill 430.
  • Infill 430 provides scaffolding with a large surface area for new bone growth.
  • Infill 430 can also add additional strength to implant 400 in compression, tension, torsion, bending, shear, etc., but still allow for better bony on-growth, ingrowth and/or through-growth than if the fenestrations or interstices were completely filled with less porous material.
  • threaded portion 420 of implant 400 separately from the porous infill 430 for clarity, although in this embodiment infill 430 is a collection of many individual segments rather than an interconnected structure.
  • threaded portion 420 may also be porous, but having a different porosity than infill 430, as previously described. Both may be made together in the same manufacturing process, such as 3D printing or other additive manufacturing process.
  • porous infill 430 has the same inner diameter as that of through bore 424, forming a continuous inner surface as shown in FIG. 20 .
  • the outer diameter of infill 430 may be the same diameter of the radially inward end of the tapered portions of threads 426, thereby forming the root diameter of threads 426. In this embodiment, these diameters are also equal to the outer diameter of mid-section 414.
  • the inner and outer diameters of counter-rotating support structure 428 may also be the same as those of infill 430, such that breaks 432 are formed in infill 430 (as seen in FIG. 19 ) to accommodate structure 428.
  • the implant site may be prepared by forming a round bore into the bone having a diameter approximately equal to the root diameter of threads 426.
  • Implant 400 may be provided with self-boring and/or self-tapping features.
  • Implant 400 may be implanted by inserting a hexagonal driver (not shown) into socket 422 and rotating implant 400 until head portion 418 contacts, becomes flush with or recessed within the outer bone surface.
  • Bone chips may be packed into through bore 424 to aid in bone growth to further secure implant 400 as it heals in place.
  • implant 450 comprises a main body 460, a proximal screw cap 462, a proximal screw 464, and a pair of rotation stops 466.
  • Proximal screw 464 comprises a head portion 468 and a shaft portion 470.
  • Shaft portion 470 may be provided with external threads (not shown) for threadably engaging with internal threads (not shown) located in the proximal end of central bore 472 which passes through main body 460.
  • proximal screw cap 462 is captivated between head portion 468 of proximal screw 464 and the proximal end of main body 460.
  • Rotation stops 466 are recessed within curved slots 474 in proximal screw cap 462 (as best seen in FIGS. 23 and 24 ) such that they prevent or inhibit counter-clockwise rotation of proximal screw head portion 468 relative to proximal screw cap 462.
  • the distal end of implant 450 may be provided with threads 476 configured to engage with a bone segment.
  • the threads 476 have a non-symmetrical longitudinal cross-section that has a saw-tooth pattern. More specifically, the proximal sides of the threads extend in a radial direction (perpendicular to the central axis of implant 450) while the distal sides of the threads are angled relative to the central axis.
  • threads 476 get progressively wider as they extend proximally (i.e.
  • the threads 476 have a transverse cross-section that is generally triangular in shape.
  • a scoop, divot or hook shape 478 may be provided on the leading edge (when rotating in an insertion direction) of each apex of the triangular-shaped threads.
  • a lateral bore 480 may also be provided to connect each scoop 478 or leading edge with central bore 472.
  • the lateral bores 480 in conjunction with the scoops 478 if provided, serve to harvest bone chips or fragments (not shown) as implant 450 is threaded into place. Bone chips may pass through lateral bores 480 and into central bore 472 where they may accumulate.
  • the bone chips may then be removed through the proximal end of central bore 472 and manually reintroduced around the implant, may be forced out the distal end of the implant with a tamper, pushed back out of lateral bores 480 once implant 450 is in the desired position, and/or may be left in place to promote bony ingrowth into implant 450.
  • the proximal side of head portion 468 of proximal screw 464 may be provided with a hexagonally shaped socket 422 for receiving a drive tool (not shown) when implant 450 is being inserted or removed.
  • the distal side of head portion 468 may be provided with a curved, convex portion 482 configured to mate with a curved, concave portion 484 located on proximal screw cap 462.
  • the circumference of the distal side of proximal screw cap 462 may be provided with a series of teeth 486 configured to bite into bone.
  • proximal screw cap 462 may freely pivot in two dimensions relative to proximal screw 464 so that most or all of the teeth 486 of screw cap 462 can engage with an outer surface of a bone segment when implant 450 is implanted therein, particularly when implant 450 is implanted in an orientation that is not orthogonal to the outer surface of the bone.
  • main body 460 is implanted first without proximal screw cap 462 or proximal screw cap 464.
  • the implant site may be prepared in a manner similar to that previously described.
  • a three-lobed driver tool (not shown) may be inserted into a mating three-lobe receptacle 488 (shown in FIG. 26 ) located at the proximal end of main body 460.
  • Main body 460 may then be threaded into the bone to a desired height, for example, such that the proximal end of main body 460 is just below the outer surface of the bone.
  • the driver tool is then removed from main body 460. Bone chips may then be packed into or moved inside central bore 472.
  • Proximal screw cap 462 may then be placed over the implant bore or over the proximal screw 464, and the distal end of proximal screw 464 may be threaded into the proximal end of main body 460.
  • a hexagonal driver tool (not shown) may be used to tighten proximal screw cap 462 against the outer surface of the bone.
  • Rotation stops 466 inhibit proximal screw 464 from backing out, as previously described. In some arrangements, rotation stops 466 may be removed from proximal screw cap 462 after implantation to allow proximal screw 468 to be rotated in the opposite direction to remove implant 450.
  • a compression spring may be provided between the proximal screw head or proximal screw cap and the proximal bone surface to maintain compression force on the joint and/or to inhibit the implant from backing out of the bone.
  • thread profiles may be utilized.
  • a buttress, V, square, multi start, tapered (root and width), variable pitch, or other thread profile may be used.
  • the ISO 5835 standard from the American National Standards Institute (ANSI) may be used for guidance.
  • Thread profiles may be designed to reduce stress concentrations. Variable thread depths may be used.
  • implants Materials that may be used to form the implants include: titanium alloy, stainless steel, ceramic, other alloys, polymers, and bone.
  • the implant or portions of the implant are additively manufactured. Porosity, fenestrations, nano tubes, nano surface treatments, hydroxyapatite, drug elution, bioactive and anti-microbial (e.g. silver) materials, coatings and/or treatments may be used to encourage bone growth and/or deliver therapeutic benefits. Porosity may vary radially, longitudinally, and/or in other manners.
  • the implants may include expandable sections and may include a modular design.
  • the implants disclosed herein may be provided in a various incremental lengths to match various anatomies.
  • the lengths range from 30 to 160 mm.
  • various incremental diameters may be provided, such as 6 to 18 mm.
  • the thread pitch is 1.5 to 10 mm.
  • the pore size of some or all of the implant is 250 to 1000 microns.
  • the porosity is 50 to 80%.
  • a threaded proximal portion configured to engage the ilium is 10 to 15 mm long, a triangular middle portion without threads is 10-15 mm long, and a distal threaded portion configured to engage the sacrum is provided in various lengths, depending on the anatomy of the particular implant site.
  • the external threads may get progressively wider as they extend proximally. This arrangement allows for the more proximal threads to press against the adjacent bone grooves more than they otherwise would to provide a tighter fit of the implant against the bone.
  • the implants disclosed herein are specifically designed to accommodate four or five zones of the sacroiliac joint. These zones can include: 1) the lateral iliac wall; 2) the ilium; 3) the SI joint itself; 4) the sacral ala; and 5) sacral vertebral body.
  • the implant design may include 1) a mechanism to lock against the lateral iliac wall (such as a series of teeth 486 on a proximal head as previously described), 2) a finer thread configured to engage the ilium, 3) fenestrations configured to be located inside the SI joint itself when the device is implanted to promote bone ingrowth and/or deliver biologics, 4) a course thread for the ala, and 5) possibly a fine thread for the sacral body.
  • Other suitable features may also be provided and configured for each of the zones, particularly the first four zones.
  • references to a structure or feature that is disposed "adjacent" another feature may have portions that overlap or underlie the adjacent feature.
  • the device may be otherwise oriented (rotated 90 degrees or at other orientations) and the spatially relative descriptors used herein interpreted accordingly.
  • the terms “upwardly”, “downwardly”, “vertical”, “horizontal” and the like are used herein for the purpose of explanation only unless specifically indicated otherwise.
  • first and second may be used herein to describe various features/elements (including steps), these features/elements should not be limited by these terms, unless the context indicates otherwise. These terms may be used to distinguish one feature/element from another feature/element. Thus, a first feature/element discussed below could be termed a second feature/element, and similarly, a second feature/element discussed below could be termed a first feature/element without departing from the teachings of the present disclosure.
  • a numeric value may have a value that is +/- 0.1% of the stated value (or range of values), +/- 1% of the stated value (or range of values), +/- 2% of the stated value (or range of values), +/- 5% of the stated value (or range of values), +/- 10% of the stated value (or range of values), etc.
  • Any numerical values given herein should also be understood to include about or approximately that value, unless the context indicates otherwise. For example, if the value "10" is disclosed, then “about 10" is also disclosed. Any numerical range recited herein is intended to include all sub-ranges subsumed therein.

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  • Health & Medical Sciences (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Surgery (AREA)
  • General Health & Medical Sciences (AREA)
  • Veterinary Medicine (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
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  • Public Health (AREA)
  • Animal Behavior & Ethology (AREA)
  • Neurology (AREA)
  • Molecular Biology (AREA)
  • Medical Informatics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Transplantation (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
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  • Neurosurgery (AREA)
  • Prostheses (AREA)
  • Surgical Instruments (AREA)

Claims (9)

  1. Gewindeimplantat (300, 400), umfassend:
    einen länglichen Hauptkörper (322, 410), der ein Außengewinde (310, 426) aufweist, das so konfiguriert ist, dass es in einen Knochen eingeschraubt werden kann; eine innere Stützstruktur (312, 428), die sich innerhalb der Außengewinde befindet und eine schraubenförmige Anordnung aufweist, die sich in einer zu den Außengewinden entgegengesetzten Richtung erstreckt,
    dadurch gekennzeichnet, dass das Implantat eine spiralförmige poröse Füllung (320, 430) zwischen den Außengewinden umfasst.
  2. Gewindeimplantat nach Anspruch 1, ferner umfassend einen Antriebssockel (315, 422), der sich an einem proximalen Ende (314, 412) des Hauptkörpers befindet und so konfiguriert ist, dass er eine Spitze eines Antriebswerkzeugs empfängt, um das Implantat rotierend in den Knochen einzutreiben.
  3. Gewindeimplantat nach Anspruch 1, ferner umfassend eine Durchgangsbohrung (316, 424), die entlang einer zentralen Längsachse des Hauptkörpers (322, 410) von einem proximalen Ende (314, 412) zu einem distalen Ende (318, 416) bereitgestellt ist.
  4. Gewindeimplantat nach Anspruch 1, wobei die Außengewinde (310, 426) einen einzigen Ansatz und die innere Stützstruktur (312, 428) vier Ansätze aufweisen.
  5. Gewindeimplantat nach Anspruch 1, wobei die innere Stützstruktur (312, 428) eine Steigung aufweist, die das Achtfache der Steigung der Außengewinde (310, 426) beträgt.
  6. Gewindeimplantat nach Anspruch 1, wobei die spiralförmige poröse Füllung (320, 430) mindestens 20 % poröser ist als die Außengewinde (310, 426) und die innere Stützstruktur (312, 428).
  7. Gewindeimplantat nach Anspruch 1, wobei der längliche Hauptkörper (322, 410) und die spiralförmige poröse Füllung (320, 430) im selben Herstellungsprozess zusammen hergestellt werden.
  8. Gewindeimplantat nach Anspruch 7, wobei der Herstellungsprozess ein additiver Herstellungsprozess ist.
  9. Gewindeimplantat nach Anspruch 1, wobei die spiralförmige poröse Füllung (320, 430) einen Kerndurchmesser der Außengewinde (310, 426) bildet.
EP19775637.2A 2018-03-28 2019-03-28 Gewindeimplantate zur verwendung über knochensegmente hinweg Active EP3773281B1 (de)

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US12427028B2 (en) 2025-09-30
EP3773281A1 (de) 2021-02-17
EP3773281A4 (de) 2022-04-06
US20190298528A1 (en) 2019-10-03
WO2019191505A1 (en) 2019-10-03
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EP4516267A2 (de) 2025-03-05
US20230210667A1 (en) 2023-07-06

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